EP2629848B1 - Ultraschall-transceiver und steuerung eines wärmeschadensprozesses - Google Patents

Ultraschall-transceiver und steuerung eines wärmeschadensprozesses Download PDF

Info

Publication number
EP2629848B1
EP2629848B1 EP11782223.9A EP11782223A EP2629848B1 EP 2629848 B1 EP2629848 B1 EP 2629848B1 EP 11782223 A EP11782223 A EP 11782223A EP 2629848 B1 EP2629848 B1 EP 2629848B1
Authority
EP
European Patent Office
Prior art keywords
signal
transceiver
ultrasonic
frequency
excitation
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
EP11782223.9A
Other languages
English (en)
French (fr)
Other versions
EP2629848A1 (de
Inventor
Ariel Sverdlik
Or Shabtay
Mark Shein-Idelson
Oleg Malafriev
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Cardiosonic Ltd
Original Assignee
Cardiosonic Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US13/049,022 external-priority patent/US20120095371A1/en
Application filed by Cardiosonic Ltd filed Critical Cardiosonic Ltd
Publication of EP2629848A1 publication Critical patent/EP2629848A1/de
Application granted granted Critical
Publication of EP2629848B1 publication Critical patent/EP2629848B1/de
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M31/00—Devices for introducing or retaining media, e.g. remedies, in cavities of the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B17/22004—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves
    • A61B17/22012—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves in direct contact with, or very close to, the obstruction or concrement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/481—Diagnostic techniques involving the use of contrast agent, e.g. microbubbles introduced into the bloodstream
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/10—Balloon catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00017—Electrical control of surgical instruments
    • A61B2017/00022—Sensing or detecting at the treatment site
    • A61B2017/00106—Sensing or detecting at the treatment site ultrasonic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B17/22004—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves
    • A61B2017/22027—Features of transducers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/32—Surgical cutting instruments
    • A61B17/320068—Surgical cutting instruments using mechanical vibrations, e.g. ultrasonic
    • A61B2017/320069—Surgical cutting instruments using mechanical vibrations, e.g. ultrasonic for ablating tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/12—Arrangements for detecting or locating foreign bodies
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/504—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of blood vessels, e.g. by angiography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00—Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F2007/0059—Heating or cooling appliances for medical or therapeutic treatment of the human body with an open fluid circuit
    • A61F2007/0063—Heating or cooling appliances for medical or therapeutic treatment of the human body with an open fluid circuit for cooling
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
    • A61M25/09—Guide wires
    • A61M2025/091—Guide wires having a lumen for drug delivery or suction
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/10—Balloon catheters
    • A61M2025/1043—Balloon catheters with special features or adapted for special applications
    • A61M2025/1052—Balloon catheters with special features or adapted for special applications for temporarily occluding a vessel for isolating a sector
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/0067—Catheters; Hollow probes characterised by the distal end, e.g. tips
    • A61M25/0068—Static characteristics of the catheter tip, e.g. shape, atraumatic tip, curved tip or tip structure
    • A61M25/007—Side holes, e.g. their profiles or arrangements; Provisions to keep side holes unblocked
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N2007/0004—Applications of ultrasound therapy
    • A61N2007/0021—Neural system treatment
    • A61N2007/0026—Stimulation of nerve tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N2007/0039—Ultrasound therapy using microbubbles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N2007/0082—Scanning transducers

Definitions

  • the present invention in some embodiments thereof, relates to an ultrasound transceiver and to control of an ablation or thermal damage process to a tissue and, more particularly, but not exclusively, to use of the transceiver in simultaneous monitoring and ablation of nearby tissue by monitoring the distance to the tissue walls, and use of change in distance between tissue walls as an indicator of progress of the thermal damage.
  • a damped receiver For the purpose of detection of effects, a damped receiver is desirable, since without damping, ringing occurs, making signals hard to read.
  • the problem is to detect the wall of an artery, or any other tissue, using an ultrasonic transceiver which is also performing the ablation and which thus must be undamped because damping will reduce efficiency. Low efficiency leads to increased heating, which can be harmful in confined spaces such as blood vessels.
  • the signal from the artery wall is drowned out by noise due to ringing and the primary echo is hard to discern. Nevertheless, detecting the echo is highly desirable in order to monitor the ablation treatment.
  • An embodiment of the present invention may analyze a sequence of sample signals.
  • the primary echo has a fixed relationship to the excitation signal, whereas the ringing signals do not.
  • the primary echo shares a main frequency component with the excitation signal although not the phase and not the amplitude. The relationship is used to distinguish the primary echo from ringing and from secondary echoes.
  • an ultrasonic transceiver apparatus for intracorporeal use comprising:
  • the signal processor is configured with an instantaneous frequency estimator to obtain an envelope of received signal minus excitation signal from the undamped ultrasonic transceiver and to use a global phase and local slopes thereof as an estimate of the instantaneous frequency, and further comprising an isolator unit for isolating signal segments whose instantaneous frequency approaches the characteristic frequency as segments containing primary echoes.
  • An embodiment may comprise a window unit for windowing the received signal using a windowing length chosen to provide windows with an expectation of a single primary echo.
  • the signal processor is further configured to find a point of appearance of a primary echo in a received signal by successively dividing the curve and fitting to a linear functions and calculating a point at which a corresponding error function is minimized.
  • An embodiment may be configured with a location unit to determine a distance to a first feature wall from the point of appearance.
  • the location unit is configured to use a second point of appearance of a further primary echo to determine a distance to a second feature wall
  • the signal processor further comprising a monitoring unit for monitoring a distance between the first feature wall and the second feature wall as an indicator of ablation progress.
  • the signal processor comprising a convolution unit for convolving an excitation signal with the received signal to carry out the isolation of the primary echo.
  • the signal processor comprises a Fourier component analyzer for isolating segments having a principle Fourier component which corresponds to a body-characteristic frequency.
  • the signal processor comprises a coherent summation unit for carrying out data summation such as to preserve amplitude and shift signals to a same phase.
  • the coherent summation unit is configured to perform coherent summation, the coherent summation comprising building an auxiliary matrix of phase weights, making a Hilbert transform and multiplying to bring all the signal to the same phase, therewith to create an in-phase sum.
  • An embodiment may comprise a reference subtracting unit configured to subtract a reference from the transceiver signal by averaging several signal samples to eliminate unstable component.
  • an ultrasonic transceiver method for intracorporeal use comprising:
  • the isolation comprises obtaining an envelope of received signal minus excitation signal from the undamped ultrasonic transceiver and using a global phase and local slopes as an estimate of the instantaneous frequency, and isolating those signal segments whose frequency approaches the instantaneous excitation frequency.
  • An embodiment may comprise windowing the received signal using a windowing length chosen to provide windows with an expectation of a single primary echo.
  • An embodiment may comprise determining a distance to a first feature wall from the point of appearance.
  • An embodiment may comprise using a second point of appearance of a further primary echo to determine a distance to a second feature wall, and monitoring a distance between the first feature wall and the second feature wall as an indicator of ablation progress.
  • An embodiment may comprise convolving an excitation signal with the received signal to carry out the isolation of the primary echo.
  • An embodiment may comprise isolating segments having a principle Fourier component which corresponds to a body characteristic frequency.
  • An embodiment may comprise carrying out coherent data summation such as to preserve amplitude and shift signals to a single phase.
  • the coherent summation comprises:
  • an ultrasonic transceiver apparatus for intracorporeal use, the apparatus comprising:
  • the body characteristic frequency may be pulse or breathing rate.
  • the signal processor is configured to obtain a power spectrum of a signal extracted from the transceiver and to identify the primary echoes from peaks in the power spectrum at the body-characteristic frequency.
  • An embodiment may comprise a coherent summation unit or a convolution unit or both.
  • a method of providing controlled thermal damage to a tissue comprising:
  • the monitoring and applying are carried out from within a blood vessel, and/ or using ultrasonics.
  • a known ablation device may be used in conjunction with an ultrasonic detector.
  • Implementation of the system of embodiments of the invention can involve performing or completing selected tasks manually, automatically, or a combination thereof. Moreover, according to actual instrumentation and equipment of embodiments of the system of the invention, several selected tasks could be implemented by hardware, by software or by firmware or by a combination thereof using an operating system.
  • a data processor such as a computing platform for executing a plurality of instructions.
  • the data processor includes a volatile memory for storing instructions and/or data and/or a non-volatile storage, for example, a magnetic hard-disk and/or removable media, for storing instructions and/or data.
  • a network connection is provided as well.
  • a display and/or a user input device such as a keyboard or mouse are optionally provided as well.
  • the present invention in some embodiments thereof, relates to an ultrasound transceiver, in particular for use in confined spaces such as blood vessel to carry out self-monitored ablation on surrounding tissues.
  • the problem is to detect the wall of an artery (or any other tissue) using an ultrasonic detector which must be undamped because damping will reduce efficiency.
  • the effectiveness of an ablation process can be determined by measuring the distance between outer and inner walls of a tissue being ablated. Specifically, as the tissue is ablated, the distance between the outer and inner walls falls, so sequential monitoring of the distance is a way of measuring the effectiveness of the ablation process.
  • the issue is that the signal from the artery wall is drowned out by noise and the ringing.
  • the primary ringing tends to share a main frequency with the excitation signal, although the phase will differ depending on the distance.
  • the frequency can be used to distinguish primary echoes from ringing and from secondary echoes as well as general noise.
  • detecting the primary echoes allows them to be used in an analysis of the entire artery wall tissue signal, and not only the face of the wall that is touching the blood.
  • the transceiver Since the transceiver is a narrow band device, it irradiates mainly at its Eigen frequency. Furthermore, voltages generated by returned pressure waves are again filtered by the transceiver, so that the primary reflected signal is an almost pure harmonic oscillation, albeit with variable amplitude. It is reasonable to expect that transient-only portions of the signal are characterized by different frequencies.
  • the present embodiments further include a means of providing controlled thermal damage to a tissue, by identifying locations of boundary walls of the tissue, applying energy to the tissue, and monitoring changes in locations of the boundary walls as indicators of the application of energy to the tissue, for example thermal shrinkage of the tissue; Then the application of the thermal energy can be controlled y according to the detected effect.
  • the monitoring and applying are carried out from within a blood vessel, and/ or using ultrasonics.
  • the above may be carried out using the transceiver described herein but alternatively, a known ablation device may be used in conjunction with an ultrasonic detector.
  • the effect on the tissue is not necessarily shrinkage. It may instead be thickening due to heating or to some physiological response. Nevertheless it is the change in size or shape of the tissue, as determined by changes in tissue wall location determined by non-imaging or imaging of tissue, that is used to control the process.
  • the present embodiments relate to non-focused ultrasound, or to focused ultrasound or to r.f. based systems.
  • FIG. 1 illustrates an ultrasonic transceiver apparatus 10 primarily intended for intracorporeal use, according to one embodiment of the present invention.
  • a transceiver 12 is designed to be injected into blood vessels and like confined spaces within the body, particularly with a view to flowing towards locations where tissue ablation is required, and to direct ultrasound energy towards the tissue to be ablated. In between ablations the transceiver is excited with monitoring signals to use ultrasound energy for a different purpose, the monitoring of the surrounding tissues to make sure that the ablation is being carried out effectively.
  • the transceiver is required to be as efficient as possible and thus to be undamped. Monitoring however requires a damped transceiver since reading the echoes is conventionally only possible once the excitations have died down. Using different transceiver surfaces for monitoring and ablation respectively is also not ideal since it is difficult to guarantee that the tissue being monitored is the same as the tissue being ablated.
  • the present embodiments thus use a single undamped transceiver for both monitoring and ablation. Structures are provided for isolating the primary reflections from ringing due to the excitation signal and due to secondary reflections from the ringing as well as assorted other noise.
  • the undamped ultrasonic transceiver may be a narrow band transceiver having a characteristic excitation frequency so that all excitations are at that characteristic frequency.
  • the primary echoes tend to share the excitation frequency, albeit at variable phases and amplitudes, whereas general ringing and tend to be at other g frequencies.
  • a signal processor 14 is connected to the transceiver 12 to isolate the primary echo signals from the ringing, secondary echoes and extraneous noise also received from the transceiver.
  • the signal processor uses presence or absence of the characteristic frequency as an isolation criterion.
  • An excitation unit 16 provides an excitation signal for the transceiver.
  • the excitation may be high power for the ablation or low power for monitoring.
  • the signal processor may have reference subtraction unit 18 which subtracts the excitation signal, from the transceiver 12.
  • the size of the segments may be chosen so that only one primary echo need be found per segment. Otherwise the presence of multiple reflections makes analysis more difficult.
  • the distances between tissue walls are known in general terms so segment lengths are chosen to represent distances smaller than the distance between walls.
  • a window unit 22 windows the received signal using a windowing length chosen to provide segments with an expectation of a single primary echo.
  • segment isolator can find primary echoes.
  • a convolution unit 20 convolves an excitation signal with the received signal to isolate only those waveforms having a high coherence with the excitation signals.
  • a coherent summation unit 27 carries out data summation such as to preserve amplitude and shift signals to the same phase.
  • the coherent summation unit may build an auxiliary matrix and then multiplies it with previously carried out Hilbert transform to shift the obtained complex analytic signals to the same phase and to make in-phase (coherent) summation
  • Coherent summation is discussed in greater detail below.
  • Fig. 4 discusses double coherent summation and convolution as a way to obtain the primary echoes.
  • Reference subtracting unit 18 may subtract a reference from the transceiver signal by averaging several signal samples (particular records), simply to eliminate unstable components and obtain the actual excitation.
  • a separate reference signal is known to be free of echoes in the region of interest. Thus, its subtraction from the particular signal reliably provides us with almost pure echo, except for the noise component.
  • the signal processor may find a point of appearance of a primary echo in the segment by successively dividing the envelope curve while fitting to a linear function and calculating a point at which a corresponding error function is minimized. Such a process is illustrated in Fig. 6 below.
  • the point of error minimization is most probably the point of onset of the primary echo and indicates the distance to a structure such as a tissue wall. Such an error minimization is shown in Fig. 7 discussed below.
  • a location unit 24 determines the distance to a first feature wall based on the point of appearance.
  • the location unit may then use a second point of appearance of a further primary echo to determine a distance to a second feature wall.
  • a process monitoring unit then calculates and monitors the distance between the first feature wall and the second feature wall as an indicator of ablation progress. As the ablation progresses the wall typically shrinks as the tissue dries out.
  • the signal processor uses correlation with a body-characteristic frequency as an isolation criterion.
  • a body-characteristic frequency is to obtain a power spectrum of the signal extracted from the transceiver and to identify the primary echoes from peaks in the power spectrum at the body-characteristic frequency.
  • the Fourier component analysis may be used instead of or in addition to coherent summation and to convolution using a convolution unit.
  • an envelope of the oscillating signal is obtained, and a global phase and its local slopes are used as estimations of instantaneous frequency (actually, instantaneous frequency is local slope itself). Also instantaneous frequency is estimated from the entire signal in analytical form, as time derivative of phase. The appearance of a primary reflection signal is then recognized within the overall envelope as a transition at an instantaneous frequency of the signal.
  • the transceiver frequency remains constant.
  • the Hilbert transform is carried out on a residual signal, after reference subtraction. The results are used for coherent summation of original signals. signal construction the Hilbert transform effectively creates a signal shifted by a quarter of a period with respect to the original signal. For a true harmonic signal, the phase of the obtained complex analytic signal - see Fig. 5B , grows linearly in time. If a new harmonic component appears in the signal, it may be revealed by a change of the phase - time curve slope.
  • a new harmonic component may be taken as the indication of a new feature that is being detected, say the near surface of a tissue in question, and a second new harmonic component may indicate the far surface of the tissue in question artery wall.
  • an algorithm for minimum total error may be used. As illustrated in Fig. 6 , the entire curve may be divided in two parts and each part may then be fitted to a linear function. We consider double fitting of the entire error as a function of the separation point. The assumption is that for the true separation point between two frequency regions the overall error reaches its minimum. In general, a change in best slope indicates the appearance of a new event. The point where the new harmonic is added turns out to be derivable from the error function. The overall error of the two curve fitting operations is a function of the point of appearance of the new harmonic, and minimization of the overall error may indicate the point. Fig. 7 illustrates such an error function with a clear minimization point.
  • the excitation voltage generates mechanical oscillations in the transceiver, which irradiate pressure waves into surrounding media. Return pressure waves generate a reflection voltage signal. It is reasonable to expect that the reflection retains at least a partial correlation with the excitation voltage.
  • An alternative or additional approach is just to convolve part of the excitation signal with the rest of the data. The reflection may thus be amplified according to the correlation and become more recognizable.
  • Fig. 8 illustrates local slopes of a phase-distance curve. Over the full phase - time (distance) curve one can evaluate local standard statistical parameter correlation coefficients. For perfectly linear dependence between two values the correlation coefficient is ⁇ 1. For noisy data or for nonlinear dependence, the absolute value is less than 1. A stable and significant decrease of correlation coefficient serves as a reliable sign of useless noisy data and allows the irrelevant signal to be excluded.
  • correlation coefficients can thus be used to find parts of the data where there are strong echoes and ignore parts where such strong echoes are absent.
  • the present embodiments were applied experimentally to estimate distance within the interval 0.19 - 5.19 mm.
  • in vitro experiments it is possible to control distance between transceiver and reflective object (metal plate) by means of a positioning device with a ruler and set it in parallel to the transceiver surface. Accuracy of 0.1 mm is available.
  • in vitro experimentation is used to generate a calibration curve between measured and actual distances. That is, to the experiment finds slope and intercept. The slope is expected to be close to 1. The intercept allows for elimination of systematic error in the ruler reading. Indeed, the intercept is not the interesting point, although technically necessary.
  • the indication of evaluation correctness is that the evaluated points lie on a straight line with a slope close to 1.
  • the sample equivalent is a reciprocal sampling frequency. For 800 MHz, it is 1.25 ns.
  • the sample equivalent is half of the sampling period multiplied by sound velocity. Its interpolated value at 23° C is 1489 m/s. Thus, a distance equivalent is 9.306-10-4 mm.
  • Fig. 2 upper part presents a raw signal and the lower part shows the same after reference subtraction.
  • Fig. 3 upper part shows averaging and gives a ratio of maximum amplitude over noise standard deviation to be 5.86.
  • the signal shown represents results of averaging 11 particular signals.
  • the lower part of Fig. 3 shows coherent summation and manages to achieve a ratio of maximum amplitude over noise standard deviation of 10.2, nearly double the level achieved by averaging.
  • the best improvement of SNR for 11 particular signals is 3.32. It follows from Fig. 3 that the real improvement is 1.74. Specifically, the improvement is the ratio of SNRs after and before processing. SNR after processing is 10.2, and SNR before is 5.96. SNR after processing is greater.
  • Figures 5A - 8 are as discussed above and illustrate estimated and real distance results for distances of 0.19mm or 0.69mm.
  • Fig. 5A shows the raw signal and
  • Fig. 5B shows the corresponding analytical signal.
  • Fig. 6 shows the curve fitting to find the point at which the primary echo component appears.
  • Fig. 7 illustrates the error function and
  • Fig. 8 illustrates the full phase-distance curve from which local slopes can be obtained.
  • Figures 9A - 12 illustrate corresponding estimated and real distance data for a distance of 1.19mm.
  • Fig. 9A shows the raw signal and
  • Fig. 9B shows the corresponding analytical signal.
  • Fig. 10 shows the fitting.
  • Fig. 11 illustrates the error function and
  • Fig. 12 illustrates the full phase-distance curve.
  • Figs 13A - 16 illustrate results for a distance of 1.69mm.
  • Fig. 13A shows the raw signal and
  • Fig. 13B shows the corresponding analytical signal.
  • Fig. 14 shows the fitting.
  • Fig. 15 illustrates the error function and
  • Fig. 16 illustrates the full phase-distance curve.
  • Figs 17 - 20 illustrate results for a distance of 2.19mm.
  • Fig. 17A shows the raw signal and Fig. 17B shows the corresponding analytical signal.
  • Fig. 18 shows the fitting.
  • Fig. 19 illustrates the error function and Fig. 20 illustrates the full phase-distance curve.
  • Figs 21A - 24 illustrate results for a distance of 2.69mm.
  • Fig. 21A shows the raw signal and
  • Fig. 21B shows the corresponding analytical signal.
  • Fig. 22 shows the fitting.
  • Fig. 23 illustrates the error function and
  • Fig. 24 illustrates the full phase-distance curve.
  • Figs 25A - 28 illustrate results for a distance of 3.19mm.
  • Fig. 25A shows the raw signal and Fig. 25B shows the corresponding analytical signal.
  • Fig. 26 shows the fitting.
  • Fig. 27 illustrates the error function and Fig. 28 illustrates the full phase-distance curve.
  • Figs 29A - 32 illustrate results for 3.69mm.
  • Fig. 29A shows the raw signal and Fig. 29B shows the corresponding analytical signal.
  • Fig. 30 shows the fitting.
  • Fig. 31 illustrates the error function and Fig. 32 illustrates the full phase-distance curve.
  • Figs 33A - 36 illustrate results for a distance of 4.19mm.
  • Fig. 33A shows the raw signal and
  • Fig. 33B shows the corresponding analytical signal.
  • Fig. 34 shows the fitting.
  • Fig. 35 illustrates the error function and
  • Fig. 36 illustrates the full phase-distance curve.
  • Figs 37A - 40 illustrate results for a distance of 4.69mm.
  • Fig. 37A shows the raw signal and
  • Fig. 37B shows the corresponding analytical signal.
  • Fig. 38 shows the fitting.
  • Fig. 39 illustrates the error function and
  • Fig. 40 illustrates the full phase-distance curve.
  • Figs 41A - 44 illustrate the results for a distance of 5.19mm.
  • Fig. 41A shows the raw signal and
  • Fig. 41B shows the corresponding analytical signal.
  • Fig. 42 shows the fitting.
  • Fig. 43 illustrates the error function and
  • Fig. 44 illustrates the full phase-distance curve.
  • a correlation curve is obtained by fitting measured results to actual distances.
  • a straight line is fitted to the data points, with slope 0.89 and intercept 0.18 mm. Correlation of known and estimated distances is high, and the observed correlation coefficient is 0.9954.
  • the procedure is now considered in more detail. It is required to estimate distance from a transceiver surface to artery wall.
  • the range of interest lies between 1...5 mm. Allowed error is 0.2 mm. Processing time is not intended to exceed 2s.
  • the reflected signal is typically small. That is, first, it is corrupted by noise in general and, second, is distorted by a residual excitation signal, otherwise known as ringing. As mentioned, the ringing can produce second order effects such as echoes of the ringing.
  • the reflected signal is a superposition of multiple similar signals each produced by its own source the source. That is, the shape of reflected signal may vary depending on the angular position of the transceiver.
  • applied transceivers are narrow band devices and reflected signals are close to harmonic, however, with variable amplitude. This allows for efficient signal isolation.
  • Data are built as a matrix, whose columns represent a reaction wherein a single record maps to a single pulse. Then, columns of the records are divided into groups on which averaging is carried out. Following this, each column is processed on the basis of the averaged groups and overall results are averaged.
  • row size may represent the total number of points recorded in a single echo response, and the column numbers may represent the total number of echo responses which was recorded.
  • a reference signal is obtained by averaging of several records.
  • phases of reflected signals are randomly different from each other, and averaging weakens this component.
  • the excitation pulse is taken as stable so averaging does not cause any deterioration.
  • the unstable component is more or less efficiently eliminated from the processed signal.
  • Noise levels may be estimated from a remote part of a record where reflections are not expected.
  • the procedure identifies the primary echo based on coherent summation.
  • a set of signals which are expected to be similar to each other. Ideally, all signals would be the same, except for the noise component. Thus summation of N such signals increases the entire signal N times while noise increases only N times. As a result, the SNR improvement is N times.
  • the described procedure becomes less efficient. This can be solved by means of a Hilbert transform producing a complex analytic signal, in which each signal can be assigned a phase, which, for a true harmonic signal would be the true phase.
  • the denominator provides proper normalization such that entries of the above weights matrix are true phase exponents.
  • the upper index H means matrix Hermit conjugation (or Hermitian conjugation), which is transposition together with complex conjugation.
  • a first factor in equation 3 is the analytic signal corresponding to the entire set of signals.
  • a second factor is an auxiliary phase weight matrix, which provides summation with proper phases.
  • S3 Reference subtraction.
  • individual subtraction is used. That is to say, for each set of data, the reference signal is multiplied by an individual scaling factor which is close to 1. The scaling factor is evaluated using the initial portion of data (below 1 mm). Individual scaling factors provide the least RMS error being applied to a particular signal, but to a portion, which is not involved in further processing. In the present embodiments, these values are propagated to the remaining portion of the data for more efficient subtraction of the excitation signal. z ⁇ z - z ref .
  • S4 Averaging. Each group of columns is averaged. Members of the group participate in the coherent summation procedure. In an embodiment, an optimal arrangement of groups is used. In this arrangement, within each group, phases are closer to each other.
  • S7 Actual transceiver frequency evaluation.
  • S8 is shown in greater detail in Fig. 47 .
  • phase curve is divided into small pieces (about 100 samples), and for each piece a local strip and a normalized linear fitting error are evaluated.
  • local slopes are obtained on overlapping pieces.
  • An instantaneous frequency may be found at each point.
  • instantaneous frequencies may be obtained by usage of a formally exact definition of frequency as a phase time derivative.
  • a Hilbert transform of the derivative may be involved.
  • a first factor in the above is a standard windowing factor (Hanning, Gauss, Kaiser, etc.).
  • a size of the window may correspond to 2 periods.
  • This second definition is used when the noise level is found to be too high. Sometimes extremely stretched signals are observed. Dimensionless factors in these formulas are established based on visual analysis of the processed signal and may be subjected to fine tuning.
  • reflected signals start at a relatively high level and do not fall below a threshold. Such would be an indication that the origin is closer than 0.95 mm.
  • SNR max A ⁇ noise .
  • Fig. 1 presents a raw signal and the same after reference subtraction.
  • Fig. 2 presents results of just averaging 11 particular signals vs. coherent summation.
  • the best improvement of SNR for 11 particular signals is 3.32. It follows from Fig. 3 that the real improvement is 1.74 based on the SNR values shown and as discussed above.
  • Figs. 48 - 51 illustrate an approach based on grouping of samples according to relationships between the echo signals, body frequencies such as pulse or breathing, and the original excitation.
  • the relative position of tissues within the body changes over short times due to breathing and blood pulsation.
  • Ultrasonic echoes from tissues obey such a periodicity whereas ringing artifacts and other types of noises do not. This is specifically true for ultrasonic echoes measured intravascularly. Consequently, the existence of such periodicity can be utilized to separate between tissue reflection and other noise sources in echoes with low signal to noise ratio.
  • Figure 48 (upper left part) shows the echo response of consecutive trials as a function of distance. A clear periodic change in the echo response from the tissue is observed.
  • the characteristic frequency profiles due to tissue movement are used to separate between the characteristic frequencies and ringing artifacts and other noise signals.
  • the catheter moves at similar frequencies to the blood pressure, as illustrated in the right part of Fig. 48 .
  • the echo readings due to catheter ringing as well as other noises are not influenced by the blood pulsation.
  • the echo signal distance can be distinguished from the background by the fact that it moves backward and forward in correspondence to the blood pulsation.
  • separating the signals that show the periodicity of the blood pressure movement from other noises may help to identify primary tissue echoes even though their signal to noise ratio is low. This allows accurate detection of the distance to the tissue wall.
  • consecutive echo signals are first collected and the power spectrum is calculated for every point in the echo along consecutive trials. This is illustrated in figure 49 which shows the power spectrum of each point of the echo. Each point corresponds to a different distance.
  • the power spectrum intensity is color coded from blue to red.
  • the ratio between the frequency components of breathing and blood pulsation, which were estimated as described earlier, and the frequency components of noise and ringing are calculated for each point of the echo signal.
  • the response ratio is defined as the reflection profile and is used to separate tissue reflections from other noises.
  • Fig. 50 The results of such a process are illustrated in Fig. 50 .
  • the upper part of Fig. 50 shows 256 consecutive echo trials as a function of distance. Echo intensity is color coded from blue to red.
  • the middle part shows five superimposed individual trials.
  • the variability profile between different signals during the ringing is different from the variability during reflections. These changes in variability are reflected in the power spectrum over consecutive echoes.
  • the lower part of Fig. 50 is a plot of the reflection profile (in blue).
  • a smoothed reflection profile (green) is obtained using a median filter.
  • a rise in this profile indicates reflections from the tissue due to increase in frequencies associated with blood pressure and breathing.
  • the distance from the artery can be identified using a threshold crossing of the smoothed reflection intensity function, the green line in Fig 50 .
  • the threshold is automatically detected by analyzing the spectrum of points with no tissue reflections, which points are detected using their low kurtosis values.
  • Fig. 51 a summary of the procedure to achieve the above is as follows: Firstly, in 51.1, the power spectrum analysis over the same sample in consecutive echos is performed. In the given example ( Fig 50 ), the echo signal is recorded 256 times, to form 256 records at a sampling frequency of 400 Hz. Within each record, 10000 points are sampled at 800 MHz.
  • a power spectrum is calculated for each point over the 256 consecutive trials, giving 10000 power spectrum graphs each being 256 samples in length.
  • the reflection intensity of every point is calculated by using the freq. ratio between the blood pressure frequencies and noise frequencies at each point (S51.2).
  • Tissue reflections are identified by their high reflection intensity (S51.3).
  • the tissue wall location is identified using an automatically detected threshold.
  • Reliable measurement may require transceiver - tissue boundary distances which are greater than 1 mm and up to 5 mm.
  • Signal acquisition is performed at 800 MHz/14 bit, and with a suitable oscilloscope such as that produced by AgilentTM, the sampling rate may be increased to 2 GHz, but at a modest 8 bit resolution.
  • transceiver characteristic frequency about 10 and 20 MHz, time resolution is 80 - 40 samples per period.
  • PRF 400 Hz which for 1000 repetitions constitutes a measurement duration of 2.5 s. This is enough to observe at least one entire period of heart pulse and therefore a full cycle of an artery dilating and shrinking. This linkage may facilitate distance measurement. In the experiments above there was processing of only 256 repetitions, using about 9000 samples each. At a PRF of 80 kHz, the entire measurement may take 3.2 ms. This time is too short for significant changes in mutual orientation of transceiver and tissue boundary, or distance between the transceiver and tissue boundary, and thus is expected to improve accuracy. In addition, a long acquisition process provides mutual incoherence of reflected signals which weakens the reflected signal level in the reference.
  • the transceivers are narrow band. Their advantage is that the main component of their signal is at the Eigen frequency at different excitation shapes. Reflected signal appearance is seen clearly using the Hilbert transform and direct evaluation of local slopes of the phase - time curve. Another possibility is to create a Hilbert transform based instantaneous frequency. A special excitation shape may shorten transient reaction and therefore decrease the low measurement limit.
  • an Eigen frequency is supplied for the transceiver, it is reasonable to make a data-based estimation. Due to variable amplitude, an instantaneous frequency may change within certain limits even for a pure single-frequency signal. Thus, the frequency may be found from local slopes, which fall within predefined tolerances of the transceiver (say, ⁇ 15%) and provide the smallest linear fitting errors. Parts of the data subjected to coherent summation are those which correspond to points which have a frequency that is close to the nominal transceiver frequency. Optionally, all entries of the instantaneous frequency matrix can be subjected to a logical operation which returns true if the frequency falls within the predetermined tolerances and false otherwise. A summation over the rows indicates how suitable a current point may be for coherent summation, and then a predetermined number of the points with largest sums are taken for coherent summation. A resonant window may then amplify true frequency components.
  • Phase correction of particular signals that is bringing all signals of interest to the same phase, allows improvement in the SNR.
  • the obtained signal is convolved with a resonant window.
  • groups may be arranged such that, within each group mutual closeness is better.
  • the above processing algorithm may provide a rapidly growing envelope signal. Since the slope is large, an error due to uncertainty of the threshold (signal appearance above noise) decreases.
  • the results of processing may show some cases of multiple reflections, which do not look as though they are reflections from the same object. It is likely that there are different objects with different reflecting properties.
  • the algorithm of the present embodiments provides a relative height and a length with each peak. The present embodiments may additionally help to classify/recognize detected objects.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Public Health (AREA)
  • Animal Behavior & Ethology (AREA)
  • Veterinary Medicine (AREA)
  • Biomedical Technology (AREA)
  • General Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Medical Informatics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Molecular Biology (AREA)
  • Hematology (AREA)
  • Biophysics (AREA)
  • Anesthesiology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Physics & Mathematics (AREA)
  • Pathology (AREA)
  • Mechanical Engineering (AREA)
  • Vascular Medicine (AREA)
  • Child & Adolescent Psychology (AREA)
  • Pulmonology (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Surgical Instruments (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)
  • Dentistry (AREA)
  • Infusion, Injection, And Reservoir Apparatuses (AREA)

Claims (15)

  1. Ultraschall-Transceiver zur innerkörperlichen Verwendung, umfassend:
    einen ungedämpften Ultraschall-Transceiver, geeignet um in einen begrenzten innerkörperlichen Raum platziert zu werden, wobei der Transceiver eine charakteristische Frequenz aufweist und geeignet ist, Erregung bei der charakteristischen Frequenz zu empfangen, um einen Ablösestrahl zum Ablösen von umgebenden Gewebe zu erzeugen, und ferner geeignet ist, Erregung durch primäre Echosignale, zurückkommend von dem umgebenden Gewebe, zu empfangen;
    gekennzeichnet durch einen Signalprozessor, verbunden mit dem Transceiver, konfiguriert zum Isolieren der primären Echosignale von Lauten, sekundären Echos und belanglosen Geräuschen, ebenfalls von dem Transceiver empfangen, wobei der Signalprozessor eine Korrelation mit einer körpercharakteristischen Frequenz als Isolationskriterium verwendet.
  2. Vorrichtung nach Anspruch 1, wobei die körpercharakteristische Frequenz ein Mitglied der Gruppe, bestehend aus Impuls und Atmungsrate, ist.
  3. Vorrichtung nach Anspruch 1, wobei der Signalprozessor konfiguriert ist, ein Leistungsspektrum von einem Signal, extrahiert von dem Transceiver zu erhalten, und die primären Echos von Spitzen in dem Leistungsspektrum bei der körpercharakteristischen Frequenz zu identifizieren.
  4. Vorrichtung nach Anspruch 1, ferner umfassend eine kohärente Summierungseinheit.
  5. Vorrichtung nach Anspruch 1, ferner umfassend eine Windungseinheit.
  6. Ultraschall-Transceiver-Vorrichtung nach Anspruch 1, umfassend:
    Schaltkreise zum Identifizieren der Lage von Begrenzungswänden des Gewebes; und zum Überwachen von Lageveränderungen der Begrenzungswände als Indikatoren für eine Auswirkung der Energie auf das Gewebe; und
    zum Steuern der Anwendung von Energie auf das Gewebe entsprechend der Auswirkung.
  7. Ultraschallvorrichtung nach Anspruch 1, umfassend Schaltkreise zum Erregen des Transceivers bei einer Momentanerregungsfrequenz, um einen Ultraschall-Ablösungsstrahl zum Ablösen von umgebendem Gewebe unter Verwendung von Ablösungsimpulsen zu erzeugen; und
    in Intervallen zwischen den Ablösungsimpulsen eine Überwachung der Erregung bereitzustellen, um primäre Echosignale, zurückkommend von dem umgebenden Gewebe, auszulösen.
  8. Ultraschall-Transceiver-Vorrichtung nach Anspruch 1, wobei der Transceiver eine Momentanerregungsfrequenz hat und zum Empfangen von Erregung bei der Erregungsfrequenz, um den Ultraschall-Ablösungsstrahl zum Ablösen des umgebenden Gewebes zu erzeugen; und wobei der Signalprozessor die Anwesenheit oder Abwesenheit der Momentanerregungsfrequenz als ein Isolationskriterium verwendet.
  9. Ultraschall-Transceiver-Vorrichtung nach Anspruch 8, wobei der Signalprozessor mit einem Momentanfrequenzkalkulator konfiguriert ist, um eine Amplitude von empfangenem Signal minus Erregungssignal von dem ungedämpften Ultraschall-Transceiver zu erhalten und eine globale Phase und ein lokales Gefälle davon als eine Schätzung der Momentanfrequenz zu erhalten, und ferner umfassend eine Isolatoreinheit zum Isolieren von Signalsegmenten, deren Momentanfrequenz sich der charakteristischen Frequenz als Segmente enthaltende primäre Echos annähert.
  10. Ultraschall-Transceiver-Vorrichtung nach Anspruch 8, ferner umfassend eine Fernstereinheit zur Fensterung des empfangenen Signals unter Verwendung einer Fensterungslänge, gewählt um Fenster mit einer Erwartung eines einzelnen Primärechos bereitzustellen.
  11. Ultraschall-Empfangsvorrichtung nach Anspruch 10, wobei der Signalprozessor ferner konfiguriert ist, einen Erscheinungspunkt eines Primärechos in einem empfangenen Signal zu finden durch aufeinanderfolgendes Dividieren der Kurve, Anpassen an eine lineare Funktion und Berechnen eines Punktes, an dem eine entsprechende Fehlerfunktion minimiert wird.
  12. Ultraschall-Empfangsvorrichtung nach Anspruch 11, ferner konfiguriert mit einer Lokalisierungseinheit zum Bestimmen eines Abstands zu einer ersten Merkmalswand von dem Erscheinungspunkt und konfiguriert zur Verwendung eines zweiten Erscheinungspunkts eines weiteren Primärechos zum Bestimmen eines Abstands zu einer weiteren Merkmalswand, wobei der Signalprozessor eine Überwachungseinheit zum Überwachen eines Abstands zwischen der ersten Merkmalswand und der zweiten Merkmalswand als ein Indikator des Ablösungsfortschritts umfasst.
  13. Ultraschallvorrichtung nach Anspruch 8, wobei der Signalprozessor eine Windungseinheit zum Falten eines Erregungssignals mit dem empfangenen Signal umfasst, um die Isolierung des Primärechos zu bewerkstelligen.
  14. Ultraschallvorrichtung nach Anspruch 8, ferner umfassend eine Referenz-Subtraktionseinheit, konfiguriert zum Subtrahieren einer Referenz von dem Transceiver-Signa durch Durchschnittsbestimmung mehrerer Signalproben.
  15. Vorrichtung nach einem der Ansprüche 1-14, wobei der Ultraschall-Ablösestrahl nicht fokussiert ist.
EP11782223.9A 2010-10-18 2011-10-18 Ultraschall-transceiver und steuerung eines wärmeschadensprozesses Active EP2629848B1 (de)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US39394710P 2010-10-18 2010-10-18
US201161453239P 2011-03-16 2011-03-16
US13/049,022 US20120095371A1 (en) 2010-10-18 2011-03-16 Ultrasound transducer and cooling thereof
PCT/IB2011/054639 WO2012052925A1 (en) 2010-10-18 2011-10-18 An ultrasound transceiver and control of a thermal damage process

Publications (2)

Publication Number Publication Date
EP2629848A1 EP2629848A1 (de) 2013-08-28
EP2629848B1 true EP2629848B1 (de) 2014-10-08

Family

ID=44993632

Family Applications (3)

Application Number Title Priority Date Filing Date
EP11782223.9A Active EP2629848B1 (de) 2010-10-18 2011-10-18 Ultraschall-transceiver und steuerung eines wärmeschadensprozesses
EP11784782.2A Withdrawn EP2661304A1 (de) 2010-10-18 2011-10-18 Therapeutika-reservoir
EP11833950.6A Active EP2629736B1 (de) 2010-10-18 2011-10-18 Gewebebehandlung

Family Applications After (2)

Application Number Title Priority Date Filing Date
EP11784782.2A Withdrawn EP2661304A1 (de) 2010-10-18 2011-10-18 Therapeutika-reservoir
EP11833950.6A Active EP2629736B1 (de) 2010-10-18 2011-10-18 Gewebebehandlung

Country Status (5)

Country Link
US (4) US20130218068A1 (de)
EP (3) EP2629848B1 (de)
JP (1) JP2013543423A (de)
CN (1) CN103298441A (de)
WO (3) WO2012052920A1 (de)

Families Citing this family (78)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8241274B2 (en) 2000-01-19 2012-08-14 Medtronic, Inc. Method for guiding a medical device
US8150519B2 (en) 2002-04-08 2012-04-03 Ardian, Inc. Methods and apparatus for bilateral renal neuromodulation
US7617005B2 (en) 2002-04-08 2009-11-10 Ardian, Inc. Methods and apparatus for thermally-induced renal neuromodulation
US20040082859A1 (en) 2002-07-01 2004-04-29 Alan Schaer Method and apparatus employing ultrasound energy to treat body sphincters
EP2021846B1 (de) 2006-05-19 2017-05-03 Koninklijke Philips N.V. Ablationsvorrichtung mit optimiertem eingangsleistungsprofil
US20080039746A1 (en) 2006-05-25 2008-02-14 Medtronic, Inc. Methods of using high intensity focused ultrasound to form an ablated tissue area containing a plurality of lesions
WO2011053757A1 (en) 2009-10-30 2011-05-05 Sound Interventions, Inc. Method and apparatus for treatment of hypertension through percutaneous ultrasound renal denervation
US20110112400A1 (en) * 2009-11-06 2011-05-12 Ardian, Inc. High intensity focused ultrasound catheter apparatuses, systems, and methods for renal neuromodulation
EP2629848B1 (de) 2010-10-18 2014-10-08 Cardiosonic Ltd. Ultraschall-transceiver und steuerung eines wärmeschadensprozesses
US8696581B2 (en) 2010-10-18 2014-04-15 CardioSonic Ltd. Ultrasound transducer and uses thereof
US9028417B2 (en) 2010-10-18 2015-05-12 CardioSonic Ltd. Ultrasound emission element
US9566456B2 (en) 2010-10-18 2017-02-14 CardioSonic Ltd. Ultrasound transceiver and cooling thereof
KR20230145213A (ko) 2011-01-19 2023-10-17 프랙틸 헬쓰, 인코포레이티드 조직의 치료를 위한 장치 및 방법
JP6441679B2 (ja) 2011-12-09 2018-12-19 メタベンション インコーポレイテッド 肝臓系の治療的な神経調節
CN104244856B (zh) * 2011-12-23 2017-03-29 维西克斯血管公司 重建身体通道的组织或身体通路附近的组织的方法及设备
AU2013215164A1 (en) * 2012-01-30 2014-08-14 Vytronus, Inc. Tissue necrosis methods and apparatus
AU2013226062B2 (en) 2012-02-27 2017-10-19 Fractyl Health, Inc. Heat ablation systems, devices and methods for the treatment of tissue
US10357304B2 (en) 2012-04-18 2019-07-23 CardioSonic Ltd. Tissue treatment
JP6235559B2 (ja) 2012-04-19 2017-11-22 フラクティル ラボラトリーズ インコーポレイテッド 組織拡張デバイス、システムおよび方法
CN104519817B (zh) 2012-04-24 2017-11-10 西比姆公司 用于颈动脉体摘除的血管内导管和方法
CN104394933A (zh) * 2012-04-27 2015-03-04 美敦力阿迪安卢森堡有限公司 肾神经调制的超声装置、系统、和方法
WO2013165935A1 (en) * 2012-05-03 2013-11-07 Sound Interventions, Inc. Apparatus and method for uniform renal denervation
US11357447B2 (en) 2012-05-31 2022-06-14 Sonivie Ltd. Method and/or apparatus for measuring renal denervation effectiveness
US9398930B2 (en) 2012-06-01 2016-07-26 Cibiem, Inc. Percutaneous methods and devices for carotid body ablation
US9402677B2 (en) 2012-06-01 2016-08-02 Cibiem, Inc. Methods and devices for cryogenic carotid body ablation
WO2014005155A1 (en) 2012-06-30 2014-01-03 Cibiem, Inc. Carotid body ablation via directed energy
EP3714826A1 (de) 2012-07-30 2020-09-30 Fractyl Laboratories, Inc. Systeme und vorrichtungen zur ablation und behandlung von gewebe
WO2014026055A1 (en) 2012-08-09 2014-02-13 Fractyl Laboratories Inc. Ablation systems, devices and methods for the treatment of tissue
US9060745B2 (en) 2012-08-22 2015-06-23 Covidien Lp System and method for detecting fluid responsiveness of a patient
US9357937B2 (en) 2012-09-06 2016-06-07 Covidien Lp System and method for determining stroke volume of an individual
US9241646B2 (en) 2012-09-11 2016-01-26 Covidien Lp System and method for determining stroke volume of a patient
US20140081152A1 (en) 2012-09-14 2014-03-20 Nellcor Puritan Bennett Llc System and method for determining stability of cardiac output
EP2903626A4 (de) 2012-10-05 2016-10-19 Fractyl Lab Inc Verfahren, systeme und vorrichtungen zur durchführung mehrerer behandlungen eines patienten
US9770593B2 (en) 2012-11-05 2017-09-26 Pythagoras Medical Ltd. Patient selection using a transluminally-applied electric current
EP2914192B1 (de) 2012-11-05 2019-05-01 Pythagoras Medical Ltd. Gesteuerte gewebeablation
US8977348B2 (en) 2012-12-21 2015-03-10 Covidien Lp Systems and methods for determining cardiac output
EP2971232A1 (de) 2013-03-14 2016-01-20 ReCor Medical, Inc. Plattierungs- oder beschichtungsverfahren für ultraschallwandler
US20140276615A1 (en) * 2013-03-14 2014-09-18 Volcano Corporation Delivery catheter having imaging capabilities
EP2968984B1 (de) 2013-03-14 2016-08-17 ReCor Medical, Inc. Ultraschallbasiertes neuromodulationssystem
WO2014153502A2 (en) * 2013-03-21 2014-09-25 Weinberg Medical Physics Llc Apparatus and method for spatially selective interventional neuroparticles
JP6440682B2 (ja) 2013-03-28 2018-12-19 ユニバーシティ オブ ワシントン スルー イッツ センター フォー コマーシャリゼーション 集束超音波機器および使用方法
JP2016517750A (ja) * 2013-05-02 2016-06-20 ハリントン ダグラス シー．ＨＡＲＲＩＮＧＴＯＮ， Ｄｏｕｇｌａｓ Ｃ． 大動脈腎動脈神経節の検出と治療のための装置及び方法
WO2014188430A2 (en) 2013-05-23 2014-11-27 CardioSonic Ltd. Devices and methods for renal denervation and assessment thereof
WO2014189966A1 (en) * 2013-05-24 2014-11-27 New Star Lasers, Inc. A California Corporation Sonic endovenous catheter
EP3003461B1 (de) 2013-06-04 2019-05-01 Fractyl Laboratories, Inc. Systeme und vorrichtungen zur reduzierung des lumenoberflächenbereichs des gastrointestinaltrakts
WO2014197625A1 (en) 2013-06-05 2014-12-11 Metavention, Inc. Modulation of targeted nerve fibers
EP3003455B1 (de) 2013-06-08 2023-08-30 Lxs, Llc Systeme zur durchführung medizinischer prozeduren mit zugriff auf das lymphsystem
CN103330578B (zh) * 2013-07-19 2015-05-27 乐普（北京）医疗器械股份有限公司 一种次圆周式超声消融导管
EP3043732B1 (de) 2013-09-12 2021-04-07 Fractyl Laboratories, Inc. Systeme und vorrichtungen zur behandlung von zielgewebe
KR102284469B1 (ko) 2013-11-22 2021-08-02 프랙틸 헬쓰, 인코포레이티드 위장관에 치료 제한부를 생성하기 위한 시스템, 장치 및 방법
WO2015138795A1 (en) 2014-03-12 2015-09-17 Cibiem, Inc. Carotid body ablation with a transvenous ultrasound imaging and ablation catheter
US10959774B2 (en) 2014-03-24 2021-03-30 Fractyl Laboratories, Inc. Injectate delivery devices, systems and methods
CN106659531A (zh) 2014-05-07 2017-05-10 毕达哥拉斯医疗有限公司 受控组织消融技术
US9757535B2 (en) 2014-07-16 2017-09-12 Fractyl Laboratories, Inc. Systems, devices and methods for performing medical procedures in the intestine
EP3169260B1 (de) 2014-07-16 2019-09-25 Fractyl Laboratories, Inc. System zur behandlung von diabetes und zugehöriger erkrankungen und störungen
US11185367B2 (en) 2014-07-16 2021-11-30 Fractyl Health, Inc. Methods and systems for treating diabetes and related diseases and disorders
US20180326227A1 (en) * 2014-11-26 2018-11-15 Sonievie Ltd. Devices and methods for pulmonary hypertension treatment
US10383685B2 (en) 2015-05-07 2019-08-20 Pythagoras Medical Ltd. Techniques for use with nerve tissue
EP3457975A2 (de) 2016-05-18 2019-03-27 Pythagoras Medical Ltd. Spiralförmiger katheter
EP3463573A2 (de) 2016-06-06 2019-04-10 Sofwave Medical Ltd. Ultraschallwandler und -system
US10524859B2 (en) 2016-06-07 2020-01-07 Metavention, Inc. Therapeutic tissue modulation devices and methods
US11383106B2 (en) * 2016-11-24 2022-07-12 National Institute Of Advanced Industrial Science And Technology Ultrasound therapy system
US20180235576A1 (en) * 2017-02-22 2018-08-23 Covidien Lp Ultrasound doppler and elastography for ablation prediction and monitoring
EP3593189A1 (de) * 2017-03-10 2020-01-15 Heraeus Noblelight America LLC Vorrichtung mit einem strahlungsemitter zum aufbringen von strahlung auf ein ziel und zugehöriges verfahren
EP3600434A4 (de) 2017-03-20 2021-01-06 Sonievie Ltd. Behandlung von pulmonaler hypertonie
JP2020511290A (ja) * 2017-03-20 2020-04-16 コルフロウ セラペウティクス エージーＣｏｒｆｌｏｗ Ｔｈｅｒａｐｅｕｔｉｃｓ Ａｇ 複合ステント再灌流システム
CN111212606B (zh) * 2017-08-15 2024-03-01 皇家飞利浦有限公司 频率可调谐血管内超声设备
US11883235B2 (en) * 2017-08-15 2024-01-30 Philips Image Guided Therapy Corporation Phased array imaging and therapy intraluminal ultrasound device
EP3459596A1 (de) * 2017-09-26 2019-03-27 Koninklijke Philips N.V. Leistungseinstellung in einem magnetresonanzgeführten hochintensiven fokussierten ultraschall
RU2702440C2 (ru) * 2017-12-27 2019-10-08 Федеральное государственное автономное научное учреждение "Центральный научно-исследовательский и опытно-конструкторский институт робототехники и технической кибернетики" (ЦНИИ РТК) Устройство для лечения геморроя при непрерывном доплер-контроле
JP2022525064A (ja) * 2019-03-27 2022-05-11 ソフウェイブ メディカル リミテッド 超音波トランスデューサ及び皮膚処置システム
US11786760B2 (en) * 2019-12-10 2023-10-17 GE Precision Healthcare LLC Multi-beam neuromodulation techniques
CN111855800B (zh) * 2020-07-17 2022-04-01 西南科技大学 声学振动快速无损测定水果货架期或最佳食用期的方法
JP2023537515A (ja) * 2020-08-11 2023-09-01 ソレント・セラピューティクス・インコーポレイテッド 神経切除による肺炎症性疾患の処置
CN116803216A (zh) 2020-12-31 2023-09-22 苏维夫医疗有限公司 安装在多个印刷电路板上的多个超声波激励器的冷却
EP4108197A1 (de) 2021-06-24 2022-12-28 Gradient Denervation Technologies Systeme zur behandlung von gewebe
WO2023060199A1 (en) * 2021-10-06 2023-04-13 The Trustees Of Columbia University In The City Of New York Method and integrated system for selective removal of defective cells and edematous fluids from the lung
US20240108404A1 (en) * 2022-10-04 2024-04-04 Otsuka Medical Devices Co., Ltd. Devices, methods and systems for renal denervation

Family Cites Families (249)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4319580A (en) 1979-08-28 1982-03-16 The Board Of Regents Of The University Of Washington Method for detecting air emboli in the blood in an intracorporeal blood vessel
SE461203B (sv) 1983-01-24 1990-01-22 Svanholm Engineering Ab G Foerfarande och anlaeggning foer framstaellning av element av gasbetong
US5372138A (en) 1988-03-21 1994-12-13 Boston Scientific Corporation Acousting imaging catheters and the like
US5038789A (en) 1989-09-28 1991-08-13 Frazin Leon J Method and device for doppler-guided retrograde catheterization
US5226847A (en) 1989-12-15 1993-07-13 General Electric Company Apparatus and method for acquiring imaging signals with reduced number of interconnect wires
ATE164746T1 (de) 1990-01-12 1998-04-15 Metcal Inc Thermische atherektomievorrichtung
AU3727993A (en) 1992-02-21 1993-09-13 Diasonics Inc. Ultrasound intracavity system for imaging therapy planning and treatment of focal disease
EP0597463A3 (en) 1992-11-13 1996-11-06 Dornier Med Systems Inc Thermotherapiesonde.
US6537306B1 (en) 1992-11-13 2003-03-25 The Regents Of The University Of California Method of manufacture of a transurethral ultrasound applicator for prostate gland thermal therapy
SE502620C2 (sv) 1993-02-26 1995-11-27 Leif Nilsson Urinkateter
JP3860227B2 (ja) 1993-03-10 2006-12-20 株式会社東芝 Ｍｒｉガイド下で用いる超音波治療装置
US5467251A (en) 1993-10-08 1995-11-14 Northern Telecom Limited Printed circuit boards and heat sink structures
US20020169394A1 (en) 1993-11-15 2002-11-14 Eppstein Jonathan A. Integrated tissue poration, fluid harvesting and analysis device, and method therefor
JPH07227394A (ja) 1994-02-21 1995-08-29 Olympus Optical Co Ltd 超音波診断治療システム
US5471988A (en) 1993-12-24 1995-12-05 Olympus Optical Co., Ltd. Ultrasonic diagnosis and therapy system in which focusing point of therapeutic ultrasonic wave is locked at predetermined position within observation ultrasonic scanning range
WO1995029737A1 (en) * 1994-05-03 1995-11-09 Board Of Regents, The University Of Texas System Apparatus and method for noninvasive doppler ultrasound-guided real-time control of tissue damage in thermal therapy
US5620417A (en) 1994-07-07 1997-04-15 Cardiovascular Imaging Systems Incorporated Rapid exchange delivery catheter
US8025661B2 (en) 1994-09-09 2011-09-27 Cardiofocus, Inc. Coaxial catheter instruments for ablation with radiant energy
US6176842B1 (en) * 1995-03-08 2001-01-23 Ekos Corporation Ultrasound assembly for use with light activated drugs
US5735280A (en) 1995-05-02 1998-04-07 Heart Rhythm Technologies, Inc. Ultrasound energy delivery system and method
US5895355A (en) 1995-05-23 1999-04-20 Cardima, Inc. Over-the-wire EP catheter
DE19520749C1 (de) 1995-06-07 1996-08-08 Siemens Ag Therapiegerät mit einer Quelle akustischer Wellen
JPH09122139A (ja) 1995-10-31 1997-05-13 Olympus Optical Co Ltd 超音波治療装置
US5895356A (en) 1995-11-15 1999-04-20 American Medical Systems, Inc. Apparatus and method for transurethral focussed ultrasound therapy
US6073048A (en) 1995-11-17 2000-06-06 Medtronic, Inc. Baroreflex modulation with carotid sinus nerve stimulation for the treatment of heart failure
US7226417B1 (en) 1995-12-26 2007-06-05 Volcano Corporation High resolution intravascular ultrasound transducer assembly having a flexible substrate
US6261233B1 (en) 1996-01-05 2001-07-17 Sunlight Medical Ltd. Method and device for a blood velocity determination
US5800482A (en) 1996-03-06 1998-09-01 Cardiac Pathways Corporation Apparatus and method for linear lesion ablation
US5971949A (en) 1996-08-19 1999-10-26 Angiosonics Inc. Ultrasound transmission apparatus and method of using same
US8663311B2 (en) 1997-01-24 2014-03-04 Celonova Stent, Inc. Device comprising biodegradable bistable or multistable cells and methods of use
US5772642A (en) 1997-02-19 1998-06-30 Medtronic, Inc. Closed end catheter
JPH10248854A (ja) 1997-03-11 1998-09-22 Olympus Optical Co Ltd 超音波治療装置
US6012457A (en) 1997-07-08 2000-01-11 The Regents Of The University Of California Device and method for forming a circumferential conduction block in a pulmonary vein
FR2764516B1 (fr) 1997-06-11 1999-09-03 Inst Nat Sante Rech Med Applicateur intratissulaire ultrasonore pour l'hyperthermie
US6514249B1 (en) 1997-07-08 2003-02-04 Atrionix, Inc. Positioning system and method for orienting an ablation element within a pulmonary vein ostium
US6117101A (en) 1997-07-08 2000-09-12 The Regents Of The University Of California Circumferential ablation device assembly
US6652515B1 (en) 1997-07-08 2003-11-25 Atrionix, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6547788B1 (en) 1997-07-08 2003-04-15 Atrionx, Inc. Medical device with sensor cooperating with expandable member
US6538739B1 (en) 1997-09-30 2003-03-25 The Regents Of The University Of California Bubble diagnostics
US6500121B1 (en) 1997-10-14 2002-12-31 Guided Therapy Systems, Inc. Imaging, therapy, and temperature monitoring ultrasonic system
US6007499A (en) 1997-10-31 1999-12-28 University Of Washington Method and apparatus for medical procedures using high-intensity focused ultrasound
AU2209599A (en) 1997-12-31 1999-07-19 Pharmasonics, Inc. Methods and systems for the inhibition of vascular hyperplasia
US6077225A (en) 1998-01-23 2000-06-20 Hewlett-Packard Company Ultrasound method for enhancing image presentation when contrast agents are used
US6319241B1 (en) * 1998-04-30 2001-11-20 Medtronic, Inc. Techniques for positioning therapy delivery elements within a spinal cord or a brain
US6740082B2 (en) 1998-12-29 2004-05-25 John H. Shadduck Surgical instruments for treating gastro-esophageal reflux
US6042556A (en) 1998-09-04 2000-03-28 University Of Washington Method for determining phase advancement of transducer elements in high intensity focused ultrasound
JP4095729B2 (ja) 1998-10-26 2008-06-04 株式会社日立製作所 治療用超音波装置
US6645147B1 (en) 1998-11-25 2003-11-11 Acuson Corporation Diagnostic medical ultrasound image and system for contrast agent imaging
US6607502B1 (en) 1998-11-25 2003-08-19 Atrionix, Inc. Apparatus and method incorporating an ultrasound transducer onto a delivery member
US6296619B1 (en) 1998-12-30 2001-10-02 Pharmasonics, Inc. Therapeutic ultrasonic catheter for delivering a uniform energy dose
US6855123B2 (en) 2002-08-02 2005-02-15 Flow Cardia, Inc. Therapeutic ultrasound system
EP1769759B1 (de) 1999-05-11 2008-08-13 Atrionix, Inc. Vorrichtung zur Ultraschallablation
US6217530B1 (en) 1999-05-14 2001-04-17 University Of Washington Ultrasonic applicator for medical applications
US7778688B2 (en) 1999-05-18 2010-08-17 MediGuide, Ltd. System and method for delivering a stent to a selected position within a lumen
US6890332B2 (en) 1999-05-24 2005-05-10 Csaba Truckai Electrical discharge devices and techniques for medical procedures
FR2794961B1 (fr) 1999-06-16 2001-09-21 Global Link Finance Procede de determination du decalage temporel entre les instants de passage d'une meme onde de pouls en deux points de mesure distincts d'un reseau arteriel d'un etre vivant et d'estimation de sa pression aortique
US6235024B1 (en) 1999-06-21 2001-05-22 Hosheng Tu Catheters system having dual ablation capability
US6471694B1 (en) 2000-08-09 2002-10-29 Cryogen, Inc. Control system for cryosurgery
US7510536B2 (en) 1999-09-17 2009-03-31 University Of Washington Ultrasound guided high intensity focused ultrasound treatment of nerves
US6652547B2 (en) 1999-10-05 2003-11-25 Omnisonics Medical Technologies, Inc. Apparatus and method of removing occlusions using ultrasonic medical device operating in a transverse mode
US6695782B2 (en) 1999-10-05 2004-02-24 Omnisonics Medical Technologies, Inc. Ultrasonic probe device with rapid attachment and detachment means
US20040097996A1 (en) 1999-10-05 2004-05-20 Omnisonics Medical Technologies, Inc. Apparatus and method of removing occlusions using an ultrasonic medical device operating in a transverse mode
US20050240170A1 (en) 1999-10-25 2005-10-27 Therus Corporation Insertable ultrasound probes, systems, and methods for thermal therapy
WO2001030240A1 (en) 1999-10-27 2001-05-03 Neuroscience Toolworks, Inc. Sonar-controlled apparatus for the delivery of electromagnetic radiation
US6626855B1 (en) 1999-11-26 2003-09-30 Therus Corpoation Controlled high efficiency lesion formation using high intensity ultrasound
WO2001041655A1 (en) 1999-12-06 2001-06-14 Simcha Milo Ultrasonic medical device
WO2001045550A2 (en) 1999-12-23 2001-06-28 Therus Corporation Ultrasound transducers for imaging and therapy
US7166098B1 (en) 1999-12-30 2007-01-23 Advanced Cardiovascular Systems, Inc. Medical assembly with transducer for local delivery of a therapeutic substance and method of using same
US6451013B1 (en) 2000-01-19 2002-09-17 Medtronic Xomed, Inc. Methods of tonsil reduction using high intensity focused ultrasound to form an ablated tissue area containing a plurality of lesions
US8221402B2 (en) 2000-01-19 2012-07-17 Medtronic, Inc. Method for guiding a medical device
US6457365B1 (en) 2000-02-09 2002-10-01 Endosonics Corporation Method and apparatus for ultrasonic imaging
US20020048310A1 (en) 2000-03-07 2002-04-25 Heuser Richard R. Catheter for thermal and ultrasound evaluation of arteriosclerotic plaque
US6428477B1 (en) 2000-03-10 2002-08-06 Koninklijke Philips Electronics, N.V. Delivery of theraputic ultrasound by two dimensional ultrasound array
US6605084B2 (en) 2000-03-24 2003-08-12 Transurgical, Inc. Apparatus and methods for intrabody thermal treatment
US7025765B2 (en) * 2000-03-31 2006-04-11 Rita Medical Systems, Inc. Tissue biopsy and treatment apparatus and method
EP1296598B1 (de) 2000-05-16 2007-11-14 Atrionix, Inc. Gerät mit einem ultraschallwandlers auf einem zuführungsstück
AU6682401A (en) 2000-06-13 2001-12-24 Atrionix Inc Surgical ablation probe for forming a circumferential lesion
CA2415134C (en) 2000-07-13 2015-09-22 Transurgical, Inc. Thermal treatment methods and apparatus with focused energy application
EP1299038B1 (de) 2000-07-13 2013-01-09 ReCor Medical, Inc. Energieanwendung mit aufblasbarer, ringförmiger linse
GB2365127A (en) 2000-07-20 2002-02-13 Jomed Imaging Ltd Catheter
SG105459A1 (en) 2000-07-24 2004-08-27 Micron Technology Inc Mems heat pumps for integrated circuit heat dissipation
US6740040B1 (en) 2001-01-30 2004-05-25 Advanced Cardiovascular Systems, Inc. Ultrasound energy driven intraventricular catheter to treat ischemia
US6932771B2 (en) 2001-07-09 2005-08-23 Civco Medical Instruments Co., Inc. Tissue warming device and method
US6763722B2 (en) 2001-07-13 2004-07-20 Transurgical, Inc. Ultrasonic transducers
US7285116B2 (en) 2004-05-15 2007-10-23 Irvine Biomedical Inc. Non-contact tissue ablation device and methods thereof
US8974446B2 (en) 2001-10-11 2015-03-10 St. Jude Medical, Inc. Ultrasound ablation apparatus with discrete staggered ablation zones
US8419729B2 (en) 2001-12-04 2013-04-16 Endoscopic Technologies, Inc. Cardiac ablation devices and methods
DE60226635D1 (de) 2001-12-14 2008-06-26 Monteris Medical Inc Hyperthermiebehandlung und dazugehörige sonde
US6998898B2 (en) 2002-02-11 2006-02-14 Texas Instruments Incorporated Programmable front end for a receiving channel
US7620451B2 (en) 2005-12-29 2009-11-17 Ardian, Inc. Methods and apparatus for pulsed electric field neuromodulation via an intra-to-extravascular approach
US7162303B2 (en) 2002-04-08 2007-01-09 Ardian, Inc. Renal nerve stimulation method and apparatus for treatment of patients
US8347891B2 (en) 2002-04-08 2013-01-08 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for performing a non-continuous circumferential treatment of a body lumen
US7853333B2 (en) 2002-04-08 2010-12-14 Ardian, Inc. Methods and apparatus for multi-vessel renal neuromodulation
US6978174B2 (en) 2002-04-08 2005-12-20 Ardian, Inc. Methods and devices for renal nerve blocking
US7653438B2 (en) * 2002-04-08 2010-01-26 Ardian, Inc. Methods and apparatus for renal neuromodulation
US8145316B2 (en) 2002-04-08 2012-03-27 Ardian, Inc. Methods and apparatus for renal neuromodulation
US7617005B2 (en) 2002-04-08 2009-11-10 Ardian, Inc. Methods and apparatus for thermally-induced renal neuromodulation
US7756583B2 (en) 2002-04-08 2010-07-13 Ardian, Inc. Methods and apparatus for intravascularly-induced neuromodulation
US20030199747A1 (en) 2002-04-19 2003-10-23 Michlitsch Kenneth J. Methods and apparatus for the identification and stabilization of vulnerable plaque
US20030199768A1 (en) 2002-04-19 2003-10-23 Cespedes Eduardo Ignacio Methods and apparatus for the identification and stabilization of vulnerable plaque
US9439714B2 (en) 2003-04-29 2016-09-13 Atricure, Inc. Vacuum coagulation probes
US20040082859A1 (en) 2002-07-01 2004-04-29 Alan Schaer Method and apparatus employing ultrasound energy to treat body sphincters
US20130197555A1 (en) 2002-07-01 2013-08-01 Recor Medical, Inc. Intraluminal devices and methods for denervation
US6866662B2 (en) 2002-07-23 2005-03-15 Biosense Webster, Inc. Ablation catheter having stabilizing array
US6942677B2 (en) 2003-02-26 2005-09-13 Flowcardia, Inc. Ultrasound catheter apparatus
US7074188B2 (en) 2002-08-26 2006-07-11 The Cleveland Clinic Foundation System and method of characterizing vascular tissue
US7220233B2 (en) 2003-04-08 2007-05-22 Flowcardia, Inc. Ultrasound catheter devices and methods
US20060052774A1 (en) 2002-09-20 2006-03-09 Garrison David M Electrosurgical instrument for fragmenting, cutting and coagulating tissue
EP1539291A4 (de) 2002-09-20 2010-03-10 Flowmedica Inc Verfahren und gerät für die selektive materialabgabe über einen intrarenalen katheter
US7156816B2 (en) 2002-11-26 2007-01-02 Biosense, Inc. Ultrasound pulmonary vein isolation
CA2412856A1 (en) 2002-11-27 2004-05-27 Frederic Bodin Pharmaceutical composition for the treatment of pulmonary arterial hypertension
WO2004054448A1 (en) 2002-12-18 2004-07-01 Koninklijke Philips Electronics N.V. Ultrasonic doppler system for determining movement of artery walls
US7771372B2 (en) 2003-01-03 2010-08-10 Ekos Corporation Ultrasonic catheter with axial energy field
US8021359B2 (en) * 2003-02-13 2011-09-20 Coaptus Medical Corporation Transseptal closure of a patent foramen ovale and other cardiac defects
JP2004290462A (ja) 2003-03-27 2004-10-21 Terumo Corp アプリケータの最適位置提示システム
US7220258B2 (en) 2003-07-02 2007-05-22 Cancercure As Therapeutic probe, method and system
JP2005027907A (ja) 2003-07-07 2005-02-03 Olympus Corp 超音波手術システムおよびプローブ
US7678104B2 (en) 2003-07-17 2010-03-16 Biosense Webster, Inc. Ultrasound ablation catheter and method for its use
DE202004021951U1 (de) 2003-09-12 2013-06-19 Vessix Vascular, Inc. Auswählbare exzentrische Remodellierung und/oder Ablation von atherosklerotischem Material
US7347859B2 (en) 2003-12-18 2008-03-25 Boston Scientific, Scimed, Inc. Tissue treatment system and method for tissue perfusion using feedback control
DE602004032574D1 (de) 2003-12-31 2011-06-16 Biosense Webster Inc Umfangsmässige ablationsvorrichtungsanordnung mit dualen expandierbaren elementen
WO2005072409A2 (en) 2004-01-29 2005-08-11 Ekos Corporation Method and apparatus for detecting vascular conditions with a catheter
US7727228B2 (en) 2004-03-23 2010-06-01 Medtronic Cryocath Lp Method and apparatus for inflating and deflating balloon catheters
US7854733B2 (en) 2004-03-24 2010-12-21 Biosense Webster, Inc. Phased-array for tissue treatment
CN1942145A (zh) 2004-04-19 2007-04-04 普罗里森姆股份有限公司 带传感器结构的消融装置
US20070222339A1 (en) 2004-04-20 2007-09-27 Mark Lukacs Arrayed ultrasonic transducer
US7313442B2 (en) 2004-04-30 2007-12-25 Advanced Neuromodulation Systems, Inc. Method of treating mood disorders and/or anxiety disorders by brain stimulation
US7538425B2 (en) 2004-07-28 2009-05-26 Delphi Technologies, Inc. Power semiconductor package having integral fluid cooling
EP1799302B1 (de) 2004-07-28 2015-03-04 Ardian, Inc. Vorrichtungen für die nierennervenblockade
US7540852B2 (en) 2004-08-26 2009-06-02 Flowcardia, Inc. Ultrasound catheter devices and methods
US7824348B2 (en) 2004-09-16 2010-11-02 Guided Therapy Systems, L.L.C. System and method for variable depth ultrasound treatment
US8535228B2 (en) * 2004-10-06 2013-09-17 Guided Therapy Systems, Llc Method and system for noninvasive face lifts and deep tissue tightening
US7479106B2 (en) 2004-09-30 2009-01-20 Boston Scientific Scimed, Inc. Automated control of irrigation and aspiration in a single-use endoscope
KR20070106972A (ko) 2004-10-06 2007-11-06 가이디드 테라피 시스템스, 엘.엘.씨. 초음파 조직치료용 시스템 및 방법
EP2279698A3 (de) * 2004-10-06 2014-02-19 Guided Therapy Systems, L.L.C. Verfahren und System zur nicht invasiven kosmetischen Verbesserung von Dehnstreifen
US7883506B2 (en) 2004-11-08 2011-02-08 Boston Scientific Scimed, Inc. Devices and methods for the treatment of endometriosis
US7713210B2 (en) 2004-11-23 2010-05-11 St. Jude Medical, Atrial Fibrillation Division, Inc. Method and apparatus for localizing an ultrasound catheter
US20060173387A1 (en) 2004-12-10 2006-08-03 Douglas Hansmann Externally enhanced ultrasonic therapy
US20060135953A1 (en) 2004-12-22 2006-06-22 Wlodzimierz Kania Tissue ablation system including guidewire with sensing element
CA2604380A1 (en) 2005-04-12 2006-10-19 Ekos Corporation Ultrasound catheter with cavitation promoting surface
JP2006289098A (ja) 2005-04-12 2006-10-26 Inolase 2002 Ltd 皮膚の真空援用式光ベース治療用の装置
US7850683B2 (en) 2005-05-20 2010-12-14 Myoscience, Inc. Subdermal cryogenic remodeling of muscles, nerves, connective tissue, and/or adipose tissue (fat)
EP1895927A4 (de) 2005-06-20 2011-03-09 Medtronic Ablation Frontiers Ablationskatheter
US7819868B2 (en) 2005-06-21 2010-10-26 St. Jude Medical, Atrial Fibrilation Division, Inc. Ablation catheter with fluid distribution structures
US7628789B2 (en) 2005-08-17 2009-12-08 Pulmonx Corporation Selective lung tissue ablation
JP4402629B2 (ja) 2005-08-19 2010-01-20 オリンパスメディカルシステムズ株式会社 超音波凝固切開装置
US20090093737A1 (en) 2007-10-09 2009-04-09 Cabochon Aesthetics, Inc. Ultrasound apparatus with treatment lens
US20070142879A1 (en) 2005-12-20 2007-06-21 The Cleveland Clinic Foundation Apparatus and method for modulating the baroreflex system
US20070088346A1 (en) 2005-10-14 2007-04-19 Mirizzi Michael S Method and apparatus for varicose vein treatment using acoustic hemostasis
US7864129B2 (en) 2006-04-04 2011-01-04 Namiki Seimitsu Houseki Kabushiki Kaisha Radio frequency medical treatment device and system and usage method thereof
WO2007115307A2 (en) 2006-04-04 2007-10-11 Volcano Corporation Ultrasound catheter and hand-held device for manipulating a transducer on the catheter's distal end
WO2007127176A2 (en) 2006-04-24 2007-11-08 Ekos Corporation Ultrasound therapy system
EP2021846B1 (de) 2006-05-19 2017-05-03 Koninklijke Philips N.V. Ablationsvorrichtung mit optimiertem eingangsleistungsprofil
US7704212B2 (en) 2006-06-14 2010-04-27 Spacelabs Healthcare Reusable invasive fluid pressure monitoring apparatus and method
ATE536147T1 (de) 2006-06-28 2011-12-15 Ardian Inc Systeme für wärmeinduzierte renale neuromodulation
US8504132B2 (en) 2006-06-28 2013-08-06 Paul Friedman Methods and apparatus for assessing and improving electrode contact with cardiac tissue
EP2073884B1 (de) 2006-08-02 2018-10-10 Osprey Medical Inc. Detektion und therapie mikrovaskulärer verstopfungen
US20090221955A1 (en) 2006-08-08 2009-09-03 Bacoustics, Llc Ablative ultrasonic-cryogenic methods
US20080039727A1 (en) 2006-08-08 2008-02-14 Eilaz Babaev Ablative Cardiac Catheter System
US20080195000A1 (en) 2006-09-06 2008-08-14 Spooner Gregory J R System and Method for Dermatological Treatment Using Ultrasound
US20080183110A1 (en) 2006-09-06 2008-07-31 Davenport Scott A Ultrasound system and method for hair removal
US8192474B2 (en) 2006-09-26 2012-06-05 Zeltiq Aesthetics, Inc. Tissue treatment methods
US8728073B2 (en) 2006-10-10 2014-05-20 Biosense Webster, Inc. Multi-region staged inflation balloon
WO2008045877A2 (en) 2006-10-10 2008-04-17 St. Jude Medical, Atrial Fibrillation Division, Inc. Electrode tip and ablation system
GB0622451D0 (en) 2006-11-10 2006-12-20 Intelligent Earth Ltd Object position and orientation detection device
US7775994B2 (en) 2006-12-11 2010-08-17 Emigrant Bank, N.A. Ultrasound medical systems and related methods
US8475375B2 (en) 2006-12-15 2013-07-02 General Electric Company System and method for actively cooling an ultrasound probe
US8382689B2 (en) 2007-02-08 2013-02-26 St. Jude Medical, Atrial Fibrillation Division, Inc. Device and method for high intensity focused ultrasound ablation with acoustic lens
US8473030B2 (en) * 2007-01-12 2013-06-25 Medtronic Vascular, Inc. Vessel position and configuration imaging apparatus and methods
US8571662B2 (en) 2007-01-29 2013-10-29 Simon Fraser University Transvascular nerve stimulation apparatus and methods
US8030754B2 (en) 2007-01-31 2011-10-04 Hewlett-Packard Development Company, L.P. Chip cooling channels formed in wafer bonding gap
EP2730247B1 (de) * 2007-02-22 2017-04-26 Ramot at Tel Aviv University Ltd. Vorrichtung zur Behandlung von Blutgefässen
US9220837B2 (en) 2007-03-19 2015-12-29 Insuline Medical Ltd. Method and device for drug delivery
US9486651B2 (en) * 2007-03-30 2016-11-08 Koninklijke Philips N.V. MRI-guided HIFU marking to guide radiotherapy and other procedures
WO2008150871A1 (en) * 2007-05-30 2008-12-11 Critical Care Innovations, Inc. Process and device for selectively treating interstitial tissue
US7634315B2 (en) 2007-05-31 2009-12-15 Pacesetter, Inc. Techniques to monitor and trend nerve damage and recovery
US7460369B1 (en) 2007-06-01 2008-12-02 Advanced Micro Devices, Inc. Counterflow microchannel cooler for integrated circuits
US20090018446A1 (en) 2007-07-10 2009-01-15 Insightec, Ltd. Transrectal ultrasound ablation probe
US9044261B2 (en) 2007-07-31 2015-06-02 Ethicon Endo-Surgery, Inc. Temperature controlled ultrasonic surgical instruments
JP5014051B2 (ja) * 2007-10-09 2012-08-29 株式会社ユネクス 血管超音波画像測定方法
EP2214573B1 (de) 2007-10-26 2019-07-03 University Of Virginia Patent Foundation System zur behandlung und bilddarstellung mit ultraschallenergie und mikrobläschen
US8906011B2 (en) 2007-11-16 2014-12-09 Kardium Inc. Medical device for use in bodily lumens, for example an atrium
US20090149782A1 (en) * 2007-12-11 2009-06-11 Donald Cohen Non-Invasive Neural Stimulation
US20090163807A1 (en) 2007-12-21 2009-06-25 Sliwa John W Finger-mounted or robot-mounted transducer device
EP2092916A1 (de) * 2008-02-19 2009-08-26 Institut National De La Sante Et De La Recherche Medicale (Inserm) Verfahren zur Behandlung einer Augenkrankheit durch Verabreichung hochintensiven fokussierten Ultraschalls und entsprechende Vorrichtung
US7981092B2 (en) 2008-05-08 2011-07-19 Ethicon Endo-Surgery, Inc. Vibratory trocar
ES2398052T5 (es) 2008-05-09 2021-10-25 Nuvaira Inc Sistemas para tratar un árbol bronquial
US8133222B2 (en) 2008-05-28 2012-03-13 Medwaves, Inc. Tissue ablation apparatus and method using ultrasonic imaging
CN102149428B (zh) * 2008-07-14 2015-07-08 代理并代表亚利桑那州立大学的亚利桑那董事会 使用超声用于调节细胞活性的方法和装置
US20100049099A1 (en) 2008-07-18 2010-02-25 Vytronus, Inc. Method and system for positioning an energy source
US8585695B2 (en) 2008-07-22 2013-11-19 Hue-Teh Shih Systems and methods for noncontact ablation
US20100036293A1 (en) 2008-08-05 2010-02-11 Scott Isola HIFU treatment probe
US9173047B2 (en) 2008-09-18 2015-10-27 Fujifilm Sonosite, Inc. Methods for manufacturing ultrasound transducers and other components
US20100114082A1 (en) 2008-10-06 2010-05-06 Sharma Virender K Method and Apparatus for the Ablation of Endometrial Tissue
KR20110104504A (ko) 2008-11-17 2011-09-22 미노우 메디컬, 인코포레이티드 조직 토폴로지의 지식 여하에 따른 에너지의 선택적 축적
US8475379B2 (en) 2008-11-17 2013-07-02 Vytronus, Inc. Systems and methods for ablating body tissue
US9352174B2 (en) 2008-12-30 2016-05-31 St. Jude Medical, Atrial Fibrillation Division, Inc. Ablation system with blood leakage minimization and tissue protective capabilities
US9108037B2 (en) 2009-03-09 2015-08-18 St. Jude Medical, Atrial Fibrillation Division, Inc. Apparatus and method for tissue ablation with near-field cooling
US8540662B2 (en) 2009-03-24 2013-09-24 St. Jude Medical, Atrial Fibrillation Division, Inc. Medical devices having an atraumatic distal tip segment
US20120116221A1 (en) * 2009-04-09 2012-05-10 The Trustees Of The University Of Pennsylvania Methods and systems for image-guided treatment of blood vessels
EP2421364A4 (de) 2009-04-22 2012-10-17 Mercator Medsystems Inc Verwendung von guanethidin zur behandlung von bluthochdruck über lokale vaskuläre freisetzung
JP5702780B2 (ja) 2009-07-21 2015-04-15 ユニバーシティ オブ バージニア パテント ファウンデーション カテーテルシステム
US20120123270A1 (en) 2009-07-29 2012-05-17 Koninklijke Philips Electronics N.V. Device with integrated ultrasound transducers and flow sensor
US20110028962A1 (en) 2009-07-31 2011-02-03 Randell Werneth Adjustable pulmonary vein ablation catheter
CA2774346C (en) 2009-09-16 2019-08-20 Board Of Regents, The University Of Texas System Altering temperature in a mammalian body
US9119951B2 (en) 2009-10-12 2015-09-01 Kona Medical, Inc. Energetic modulation of nerves
US20110092880A1 (en) * 2009-10-12 2011-04-21 Michael Gertner Energetic modulation of nerves
US8986211B2 (en) 2009-10-12 2015-03-24 Kona Medical, Inc. Energetic modulation of nerves
US20140074076A1 (en) 2009-10-12 2014-03-13 Kona Medical, Inc. Non-invasive autonomic nervous system modulation
US20160059044A1 (en) 2009-10-12 2016-03-03 Kona Medical, Inc. Energy delivery to intraparenchymal regions of the kidney to treat hypertension
US9174065B2 (en) * 2009-10-12 2015-11-03 Kona Medical, Inc. Energetic modulation of nerves
US20110257563A1 (en) 2009-10-26 2011-10-20 Vytronus, Inc. Methods and systems for ablating tissue
WO2011053757A1 (en) 2009-10-30 2011-05-05 Sound Interventions, Inc. Method and apparatus for treatment of hypertension through percutaneous ultrasound renal denervation
WO2011053182A1 (ru) 2009-11-02 2011-05-05 Leontiev Vladimir Vasilievich Устройство накопления и обработки информации (унои)
US20110112400A1 (en) * 2009-11-06 2011-05-12 Ardian, Inc. High intensity focused ultrasound catheter apparatuses, systems, and methods for renal neuromodulation
EP2498705B1 (de) * 2009-11-11 2014-10-15 Holaira, Inc. Vorrichtung zur gewebebehandlung und stenosekontrolle
US9457171B2 (en) 2009-12-02 2016-10-04 Renovorx, Inc. Devices, methods and kits for delivery of therapeutic materials to a target artery
ES2928669T3 (es) 2009-12-31 2022-11-22 Zetroz Systems Llc Dispositivo de acoplamiento para ecografía
US20110201973A1 (en) 2010-02-18 2011-08-18 St. Jude Medical, Inc. Ultrasound compatible radiofrequency ablation electrode
JP5760079B2 (ja) 2010-04-14 2015-08-05 ボストン サイエンティフィック サイムド，インコーポレイテッドＢｏｓｔｏｎ Ｓｃｉｅｎｔｉｆｉｃ Ｓｃｉｍｅｄ，Ｉｎｃ． 腎動脈に除神経療法を送達する装置
US8834388B2 (en) * 2010-04-30 2014-09-16 Medtronic Ablation Frontiers Llc Method and apparatus to regulate a tissue temperature
US8617150B2 (en) * 2010-05-14 2013-12-31 Liat Tsoref Reflectance-facilitated ultrasound treatment
US20120053577A1 (en) 2010-08-25 2012-03-01 Neuwave Medical, Inc. Energy delivery systems and uses thereof
US9566456B2 (en) 2010-10-18 2017-02-14 CardioSonic Ltd. Ultrasound transceiver and cooling thereof
US9028417B2 (en) 2010-10-18 2015-05-12 CardioSonic Ltd. Ultrasound emission element
EP2629848B1 (de) 2010-10-18 2014-10-08 Cardiosonic Ltd. Ultraschall-transceiver und steuerung eines wärmeschadensprozesses
US8696581B2 (en) 2010-10-18 2014-04-15 CardioSonic Ltd. Ultrasound transducer and uses thereof
US20120215106A1 (en) 2010-10-18 2012-08-23 CardioSonic Ltd. Tissue treatment
US20130218054A1 (en) 2010-10-18 2013-08-22 CardioSonic Ltd. Separation device for ultrasound element
EP2455133A1 (de) 2010-11-18 2012-05-23 Koninklijke Philips Electronics N.V. Katheter mit kapazitiven mikrobearbeiteten Ultraschall-Transducern mit einstellbarer Brennweite
US20120232409A1 (en) 2010-12-15 2012-09-13 Stahmann Jeffrey E System and method for renal artery occlusion during renal denervation therapy
KR101862903B1 (ko) 2011-08-26 2018-05-30 사이맵 홀딩 리미티드 동맥벽 기능성 신경의 위치 확정과 식별에 사용하는 카테터 및 그 사용 방법
WO2013111136A2 (en) 2012-01-25 2013-08-01 CardioSonic Ltd. Selective reduction of nerve activity
US20130225595A1 (en) 2012-02-29 2013-08-29 Gilead Sciences, Inc. Method for treating pulmonary arterial hypertension in a patient not having idiopathic pulmonary fibrosis
AU2013230893B2 (en) 2012-03-08 2015-12-03 Medtronic Af Luxembourg S.A.R.L. Neuromodulation and associated systems and methods for the management of pain
WO2013157009A2 (en) 2012-04-18 2013-10-24 CardioSonic Ltd. Tissue treatment
US10357304B2 (en) 2012-04-18 2019-07-23 CardioSonic Ltd. Tissue treatment
CN104394933A (zh) 2012-04-27 2015-03-04 美敦力阿迪安卢森堡有限公司 肾神经调制的超声装置、系统、和方法
US20130296646A1 (en) 2012-05-02 2013-11-07 Enigma Medical, Inc. Non-invasive or minimally invasive paraspinal sympathetic ablation for the treatment of resistant hypertension
CN104470454B (zh) 2012-05-18 2018-06-08 努瓦拉公司 紧凑传送的肺部治疗系统和改善肺部功能的方法
US11357447B2 (en) 2012-05-31 2022-06-14 Sonivie Ltd. Method and/or apparatus for measuring renal denervation effectiveness
EP2900160A2 (de) 2012-09-26 2015-08-05 Boston Scientific Scimed, Inc. Katheter mit einer rippen- und wirbelsäulenstruktur zum stützen mehrerer elektroden zur nierennervenablation
CN102908191A (zh) 2012-11-13 2013-02-06 陈绍良 多极同步肺动脉射频消融导管
US9827036B2 (en) 2012-11-13 2017-11-28 Pulnovo Medical (Wuxi) Co., Ltd. Multi-pole synchronous pulmonary artery radiofrequency ablation catheter
WO2014188430A2 (en) 2013-05-23 2014-11-27 CardioSonic Ltd. Devices and methods for renal denervation and assessment thereof
US20160374710A1 (en) 2014-03-12 2016-12-29 Yegor D. Sinelnikov Carotid body ablation with a transvenous ultrasound imaging and ablation catheter
US10537387B2 (en) 2014-04-17 2020-01-21 Digma Medical Ltd. Methods and systems for blocking neural activity in an organ of a subject, preferably in the small intestine or the duodenum
US20180326227A1 (en) 2014-11-26 2018-11-15 Sonievie Ltd. Devices and methods for pulmonary hypertension treatment
EP3600434A4 (de) 2017-03-20 2021-01-06 Sonievie Ltd. Behandlung von pulmonaler hypertonie

Also Published As

Publication number Publication date
WO2012052926A2 (en) 2012-04-26
WO2012052926A3 (en) 2012-08-23
US20120265227A1 (en) 2012-10-18
JP2013543423A (ja) 2013-12-05
US20130218068A1 (en) 2013-08-22
WO2012052920A1 (en) 2012-04-26
EP2629848A1 (de) 2013-08-28
CN103298441A (zh) 2013-09-11
EP2661304A1 (de) 2013-11-13
WO2012052925A1 (en) 2012-04-26
US20130211396A1 (en) 2013-08-15
US20130204242A1 (en) 2013-08-08
EP2629736A2 (de) 2013-08-28
EP2629736B1 (de) 2017-02-22
US10967160B2 (en) 2021-04-06
EP2629736A4 (de) 2014-04-09

Similar Documents

Publication Publication Date Title
EP2629848B1 (de) Ultraschall-transceiver und steuerung eines wärmeschadensprozesses
US7894874B2 (en) Method and apparatus for enhancing the detecting and tracking of moving objects using ultrasound
US7611467B2 (en) Method and apparatus for extracting an envelope curve of a spectrogram
KR101398948B1 (ko) 진폭―위상 변조된 초음파를 이용한 점탄성 측정
CN107616809B (zh) 医学诊断超声中的组织表征
JP4263943B2 (ja) 超音波診断装置
US20070043294A1 (en) Automatic detection method of spectral Doppler blood flow velocity
US20130345565A1 (en) Measuring Acoustic Absorption or Attenuation of Ultrasound
US8226559B2 (en) Method and apparatus for real-time temperature measuring for high-intensity focused ultrasound(HIFU) therapy system
US8100832B2 (en) Ultrasound diagnostic apparatus
US11850098B2 (en) Method and device for measuring an ultrasound parameter of a viscoelastic medium
Vilkomerson et al. Finding the peak velocity in a flow from its Doppler spectrum
Ricci et al. An improved Doppler model for obtaining accurate maximum blood velocities
JPH07265304A (ja) 動脈の分節を超音波エコーグラフィにより検出し特徴付ける方法および装置
CN107106125B (zh) 用于测量动脉参数的系统和方法
Ikeshita et al. Noninvasive measurement of transient change in viscoelasticity due to flow-mediated dilation using automated detection of arterial wall boundaries
JPWO2006088094A1 (ja) 超音波ドプラ血流計
JP2010069065A (ja) 非侵襲血糖測定装置
Ibrahim et al. Detection of arterial wall boundaries using an echo model composed of multiple ultrasonic pulses
US11751851B2 (en) Methods, systems and computer program products for tissue analysis using ultrasonic backscatter coherence
Robles et al. Ultrasonic bone localization algorithm based on time-series cumulative kurtosis
JP2007090003A (ja) 超音波診断装置及びその制御方法
KR20200143285A (ko) 점탄성 매체의 초음파 파라미터를 측정하는 방법 및 디바이스
Hasegawa et al. Reduction of influence of decrease in signal-to-noise ratio in measurement of change in thickness of arterial wall due to heartbeat
Numata et al. Basic study on detection of outer boundary of arterial wall using its longitudinal motion

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

17P Request for examination filed

Effective date: 20130516

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

DAX Request for extension of the european patent (deleted)
GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

RIC1 Information provided on ipc code assigned before grant

Ipc: A61M 25/10 20130101ALN20140401BHEP

Ipc: G01N 29/46 20060101ALN20140401BHEP

Ipc: G01N 29/44 20060101ALN20140401BHEP

Ipc: A61B 17/00 20060101ALN20140401BHEP

Ipc: A61N 7/00 20060101AFI20140401BHEP

Ipc: A61M 25/00 20060101ALI20140401BHEP

INTG Intention to grant announced

Effective date: 20140424

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

REG Reference to a national code

Ref country code: GB

Ref legal event code: FG4D

REG Reference to a national code

Ref country code: AT

Ref legal event code: REF

Ref document number: 690284

Country of ref document: AT

Kind code of ref document: T

Effective date: 20141015

Ref country code: CH

Ref legal event code: EP

REG Reference to a national code

Ref country code: IE

Ref legal event code: FG4D

REG Reference to a national code

Ref country code: DE

Ref legal event code: R096

Ref document number: 602011010499

Country of ref document: DE

Effective date: 20141120

REG Reference to a national code

Ref country code: NL

Ref legal event code: VDEP

Effective date: 20141008

REG Reference to a national code

Ref country code: AT

Ref legal event code: MK05

Ref document number: 690284

Country of ref document: AT

Kind code of ref document: T

Effective date: 20141008

REG Reference to a national code

Ref country code: LT

Ref legal event code: MG4D

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: NL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20150208

Ref country code: PT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20150209

Ref country code: NO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20150108

Ref country code: ES

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: FI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: LT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: PL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: LV

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: HR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: AT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: GR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20150109

Ref country code: SE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: RS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: CY

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: BE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20141031

REG Reference to a national code

Ref country code: DE

Ref legal event code: R097

Ref document number: 602011010499

Country of ref document: DE

REG Reference to a national code

Ref country code: IE

Ref legal event code: MM4A

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MC

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: LI

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20141031

Ref country code: RO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: DK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: CH

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20141031

Ref country code: CZ

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: SK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: EE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

26N No opposition filed

Effective date: 20150709

REG Reference to a national code

Ref country code: FR

Ref legal event code: PLFP

Year of fee payment: 5

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20141018

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SM

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: BG

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: LU

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20141018

Ref country code: TR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

Ref country code: HU

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT; INVALID AB INITIO

Effective date: 20111018

REG Reference to a national code

Ref country code: FR

Ref legal event code: PLFP

Year of fee payment: 6

REG Reference to a national code

Ref country code: FR

Ref legal event code: PLFP

Year of fee payment: 7

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

REG Reference to a national code

Ref country code: FR

Ref legal event code: PLFP

Year of fee payment: 8

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: AL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20141008

REG Reference to a national code

Ref country code: DE

Ref legal event code: R081

Ref document number: 602011010499

Country of ref document: DE

Owner name: SONIVIE LTD., IL

Free format text: FORMER OWNER: CARDIOSONIC LTD., TEL-AVIV, IL

REG Reference to a national code

Ref country code: GB

Ref legal event code: 732E

Free format text: REGISTERED BETWEEN 20210617 AND 20210623

P01 Opt-out of the competence of the unified patent court (upc) registered

Effective date: 20231005

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 20231020

Year of fee payment: 13

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: FR

Payment date: 20231025

Year of fee payment: 13

Ref country code: DE

Payment date: 20231020

Year of fee payment: 13